US20100256489A1 - Handheld Transducer Scanning Speed Guides and Position Detectors - Google Patents

Handheld Transducer Scanning Speed Guides and Position Detectors Download PDF

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Publication number
US20100256489A1
US20100256489A1 US12/680,538 US68053808A US2010256489A1 US 20100256489 A1 US20100256489 A1 US 20100256489A1 US 68053808 A US68053808 A US 68053808A US 2010256489 A1 US2010256489 A1 US 2010256489A1
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United States
Prior art keywords
light sources
transducer
row
user
external ultrasound
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Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
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US12/680,538
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English (en)
Inventor
Laust G. Pedersen
Constantine C. Davlantes
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Nivasonix LLC
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Nivasonix LLC
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Priority to US12/680,538 priority Critical patent/US20100256489A1/en
Publication of US20100256489A1 publication Critical patent/US20100256489A1/en
Assigned to NIVASONIX, LLC reassignment NIVASONIX, LLC ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: DAVLANTES, CONSTANTINE C., PEDERSEN, LAUST G.
Abandoned legal-status Critical Current

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N7/00—Ultrasound therapy
    • A61N7/02—Localised ultrasound hyperthermia
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B2017/00017—Electrical control of surgical instruments
    • A61B2017/00115—Electrical control of surgical instruments with audible or visual output
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N7/00—Ultrasound therapy
    • A61N2007/0004—Applications of ultrasound therapy
    • A61N2007/0008—Destruction of fat cells

Definitions

  • the present invention relates to the field of non-invasive external ultrasound lipoplasty, skin tightening, and various non-invasive aesthetic, dermatologic, and therapeutic applications.
  • the transducer's movement or instantaneous scanning speed needs to be known or better yet its position from which the scanning speed can be easily derived.
  • U.S. Pat. No. 7,347,855 teaches a passive system of computerized tracking of a multiplicity of target volumes with compensation for body movements.
  • U.S. Pat. No. 6,645,162 teaches an active tracking system depicted in their FIGS. 12 and 13 guiding a transducer in a linear motion.
  • U.S. Pat. No. 7,150,716 is specific to diagnostic ultrasound, and teaches two methods (and systems) of detecting transducer scanning speed, namely one through the use of an sensor similar to an optical computer mouse and another through real time de-correlation of ultrasound images.
  • FIG. 1 a is a functional block diagram of one embodiment of the present invention.
  • FIG. 1 b is a functional block diagram of an alternate form of the embodiment of FIG. 1 a.
  • FIG. 2 a is a functional block diagram of another embodiment of the present invention.
  • FIG. 2 b is a functional block diagram of alternate form of the second embodiment.
  • FIG. 3 is a functional block diagram of still another embodiment of the present invention.
  • FIG. 4 is a view of a graphical user interface (e.g., touch screen display menu) with a scanning speed indicator in accordance with the embodiment of FIG. 1 a.
  • a graphical user interface e.g., touch screen display menu
  • FIG. 5 is a transducer with an integral scanning speed indicator, which in this example consists of five LEDs, in accordance with the embodiment of FIG. 1 b.
  • FIG. 6 is a flexible scanning speed guidance strip with built in LEDs in accordance with the embodiments of FIGS. 2 a and 2 b.
  • FIG. 7 is a cross sectional view of an exemplary optical sensor in accordance with still another embodiment of the present invention.
  • the optimum transducer “scanning” speed for delivering a predetermined dose of ultrasound to a desired treatment area determined by a scanning plan is a function of both the cavitation related Mechanical Index (MI) and tissue temperature Thermal Index (TI) settings. While cavitation is a threshold mechanism there is both an amplitude factor beyond the threshold level and an exposure time factor involved in emulsifying a certain fraction of the treated fat, whereby low settings require a slow scanning speed and high settings require faster scanning speeds.
  • the relationships can be estimated from the numerical values of MI and TI and further refined empirically using data from animal and clinical studies.
  • the transducer since the transducer is not 100% energy efficient, its face (skin contact area) will create heat and if not properly controlled may present a hazard for potential skin burns.
  • control of the skin heating can be included in the speed indicator. If there is no transducer face temperature sensor the suggested transducer movement speed component due to tissue heating can be based on empirical data from animal and clinical studies.
  • FIGS. 1 a and 1 b There are at least three approaches for addressing control of the ultrasound dose delivery, as summarized in FIGS. 1 a and 1 b , FIGS. 2 a and 2 b , and FIG. 3 .
  • One method requires the user to be part of the feedback loop, whereby the system, the transducer, or a separate device acts as a visual guide for the user to apply the desired scanning speed.
  • the first embodiment is an example of this approach.
  • Another method consists of a subsystem that detects the transducer scanning velocity and in real time transfers this information to the system, which in turn adjusts parameters such as MI and TI (i.e., ultrasound dose) to achieve the desired effect based on the actual speed of transducer movement. This relieves the user from precisely matching the desired scanning speed, but still requires the user to keep track of the transducer position and the ultrasound beam focal depth.
  • MI and TI i.e., ultrasound dose
  • a third method monitors the transducer position, which is transferred to the system in real time. With this information and the presence of a clock, the transducer velocity may also be easily calculated. Now the system can automatically adjust the needed parameters such as MI, TI and focal length to accomplish the planned treatment, giving the user the freedom to move the transducer almost “at will”.
  • the third embodiment is an example of this.
  • the connecting lines in the functional block diagrams in FIGS. 1 a to 3 have the following meaning.
  • the occasional user control of the system/console is shown as 7 .
  • Item 8 indicates that the user reads the scanning speed indicator.
  • Item 9 indicates that the user views the actual scanning speed of the transducer.
  • Item 10 indicates that the user actually holds and moves the transducer.
  • Item 11 shows the transmit signals from the system to the transducer.
  • Item 12 shows the low level power supply and control signals from the system to the Scanning Speed Pad 5 or optical sensor.
  • Item 13 indicates the path of sensor signals from the optical sensor to the built in Decoder, which translates the information into position and speed.
  • FIGS. 1 a and 4 are to have a visual transducer scanning speed indicator on the transmitter (main unit, console or system) that moves with the same speed that is optimal for the transducer motion on the skin.
  • the speed indicator can take the form of a moving cursor 2 on a screen 1 of the transmitter.
  • the moving cursor can take many forms, the one shown in FIGS. 1 a , 1 b , 2 a , 2 b and 4 through 6 consists of four moving dots (light sources such as LEDs). These may be sequentially switched on and off at a controlled rate, or the first switched on, the second switched on, etc. with all being switched off and the cycle repeated after the last light source has been switched on, either of which is to be considered sequential switching on, or scanning.
  • the user can then practice matching that speed while holding the transducer near the screen. When sufficiently proficient he/she can match the speed when scanning on the skin. As verification, the user can mark the skin for a certain distance and calculate the time needed to traverse that distance based on the numerical value of the desired velocity.
  • FIGS. 1 b and 5 Another version ( FIGS. 1 b and 5 ) of the first embodiment is to have a visual transducer scanning speed indicator on the transducer itself 3 , for example in the form of an array of visual indicators (light sources) such as Light Emitting Diodes (LEDs) 4 , which light up in a sequence corresponding to the desired speed of the transducer. It will then be up to the user to provide the “feedback loop” by moving the transducer at the indicated speed. Here the user can perform the same verification as described above.
  • a visual transducer scanning speed indicator on the transducer itself 3 , for example in the form of an array of visual indicators (light sources) such as Light Emitting Diodes (LEDs) 4 , which light up in a sequence corresponding to the desired speed of the transducer.
  • LEDs Light Emitting Diodes
  • a second embodiment is a separate flexible scanning speed guidance pad 5 ( FIGS. 2 a , 2 b and 6 ), which can be placed on the patient adjacent to the intended transducer path.
  • the flexible material can be silicone rubber or other material with LEDs (or other visual indicators) 6 molded in.
  • the LEDs are sequentially switched on and off so that they provide visual scanning speed guidance in proximity to the transducer.
  • the speed guidance pad can be manufactured in different lengths and/or from different materials to fit the desired treatment area, and can also be either disposable (single patient use), semi-disposable, or reusable.
  • the LEDs can be powered either by batteries, as in the embodiment of FIG. 2 a , or by the transmitter, embodiment of FIG.
  • the system may display the scanning speed, scanning location or position, and range of scan distance if the pad is physically longer than the desired scan needed to match the system settings, while the battery operated solution either would require wireless transmission of the information, or require the user to set the scanning speed according to the transmitter's displayed parameters.
  • a third embodiment is an optical 2D location sensor technology similar or identical to those used in an optical computer mouse, as in FIGS. 3 and 7 .
  • the sensor primarily consists of a light source 13 , a translucent membrane or cavity 16 , a lens 14 to collimate the reflected light from the skin 18 , which also goes through the acoustic coupling gel 19 and continues through an optical guide to an optical sensor array 20 embedded in an integrated circuit 17 .
  • the optical sensor is attached to or built into a transducer, generally like that of FIG. 5 .
  • the sensor information is passed through the transducer cable and processed in the system to find the position and velocity of the transducer. Any speckle, phase shift, frequency shift or other characteristics may be used to detect motion and velocity.
  • the sensor information may be wirelessly communicated to the system.
  • the optical 2D location sensor can lose track of the transducer position if lifted from the surface (skin). This can be overcome with a simple calibration process, whereby the user moves the transducer to a marked calibration spot on the skin, push a calibration button on the transducer or on the system, and moves the transducer on the skin to the desired location.
  • This third embodiment is very adaptable to a scanning plan in which the user graphically composes a 3D volume using software within the system or off line, showing the relative location and amount of treatment wanted, both with respect to cavitation (fat emulsification), heating (skin tightening), or other aesthetic/dermatologic/therapeutic treatments.
  • Off line use of the scanning plan software allows data transfer to the system.
  • the system can keep track of the transducer's location and in real time can adjust critical parameters such as MI, TI and focal depth (if equipped with electronic focusing), so the desired treatment “dose” eventually will be delivered.
  • the real time difference between the desired and actual delivered “dose” can also be displayed on the system graphically in a 2D format, so the user can concentrate the transducer motion in the area where more treatment is needed. This allows the user to move the transducer freely within certain boundaries with respect to both position and speed.
  • the transducer needs to be oriented perpendicular to the skin and in the case of a brush-beam transducer, the scanning velocity vector needs to be perpendicular to the brush width direction.
  • an angular error relative to the exact perpendicularity is a cosine function, meaning that it is a weak dependency, so that in reality, perpendicularity need not be monitored, but can be continuously estimated by the user.
  • the suggested speed shown by the various embodiments of the speed indicator can be based on MI, TI and instantaneous transducer face temperatures and/or acquired data from animal and clinical studies. While the above methods are intended to be used in conjunction with a non-invasive ultrasound lipoplasty transducer, the inventions, the scanning light source of the first two embodiments can be used on handheld transducers for other modalities, including aesthetic, dermatologic, or other therapeutic applications.
  • a reference to a handheld external ultrasound treatment transducer is a reference to a handheld external ultrasound transducer useable for lipoplasty, skin tightening, aesthetic, dermatologic/, and other therapeutic purposes.

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  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Ultra Sonic Daignosis Equipment (AREA)
  • Surgical Instruments (AREA)
US12/680,538 2007-09-28 2008-09-29 Handheld Transducer Scanning Speed Guides and Position Detectors Abandoned US20100256489A1 (en)

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US99589507P 2007-09-28 2007-09-28
US12/680,538 US20100256489A1 (en) 2007-09-28 2008-09-29 Handheld Transducer Scanning Speed Guides and Position Detectors
PCT/US2008/078188 WO2009043046A1 (en) 2007-09-28 2008-09-29 Handheld transducer scanning speed guides and position detectors

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US9039619B2 (en) 2004-10-06 2015-05-26 Guided Therapy Systems, L.L.C. Methods for treating skin laxity
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US9095697B2 (en) 2004-09-24 2015-08-04 Guided Therapy Systems, Llc Methods for preheating tissue for cosmetic treatment of the face and body
US9283410B2 (en) 2004-10-06 2016-03-15 Guided Therapy Systems, L.L.C. System and method for fat and cellulite reduction
US9283409B2 (en) 2004-10-06 2016-03-15 Guided Therapy Systems, Llc Energy based fat reduction
US9320537B2 (en) 2004-10-06 2016-04-26 Guided Therapy Systems, Llc Methods for noninvasive skin tightening
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US9440096B2 (en) 2004-10-06 2016-09-13 Guided Therapy Systems, Llc Method and system for treating stretch marks
US9510802B2 (en) 2012-09-21 2016-12-06 Guided Therapy Systems, Llc Reflective ultrasound technology for dermatological treatments
US9694212B2 (en) 2004-10-06 2017-07-04 Guided Therapy Systems, Llc Method and system for ultrasound treatment of skin
US9827449B2 (en) 2004-10-06 2017-11-28 Guided Therapy Systems, L.L.C. Systems for treating skin laxity
US10420960B2 (en) 2013-03-08 2019-09-24 Ulthera, Inc. Devices and methods for multi-focus ultrasound therapy
US10537304B2 (en) 2008-06-06 2020-01-21 Ulthera, Inc. Hand wand for ultrasonic cosmetic treatment and imaging
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US10864385B2 (en) 2004-09-24 2020-12-15 Guided Therapy Systems, Llc Rejuvenating skin by heating tissue for cosmetic treatment of the face and body
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US11207548B2 (en) 2004-10-07 2021-12-28 Guided Therapy Systems, L.L.C. Ultrasound probe for treating skin laxity
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US11883688B2 (en) 2004-10-06 2024-01-30 Guided Therapy Systems, Llc Energy based fat reduction
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US9320537B2 (en) 2004-10-06 2016-04-26 Guided Therapy Systems, Llc Methods for noninvasive skin tightening
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US9421029B2 (en) 2004-10-06 2016-08-23 Guided Therapy Systems, Llc Energy based hyperhidrosis treatment
US9427601B2 (en) 2004-10-06 2016-08-30 Guided Therapy Systems, Llc Methods for face and neck lifts
US9427600B2 (en) 2004-10-06 2016-08-30 Guided Therapy Systems, L.L.C. Systems for treating skin laxity
US9440096B2 (en) 2004-10-06 2016-09-13 Guided Therapy Systems, Llc Method and system for treating stretch marks
US11338156B2 (en) 2004-10-06 2022-05-24 Guided Therapy Systems, Llc Noninvasive tissue tightening system
US9522290B2 (en) 2004-10-06 2016-12-20 Guided Therapy Systems, Llc System and method for fat and cellulite reduction
US9533175B2 (en) 2004-10-06 2017-01-03 Guided Therapy Systems, Llc Energy based fat reduction
US11235179B2 (en) 2004-10-06 2022-02-01 Guided Therapy Systems, Llc Energy based skin gland treatment
US9694211B2 (en) 2004-10-06 2017-07-04 Guided Therapy Systems, L.L.C. Systems for treating skin laxity
US9694212B2 (en) 2004-10-06 2017-07-04 Guided Therapy Systems, Llc Method and system for ultrasound treatment of skin
US9707412B2 (en) 2004-10-06 2017-07-18 Guided Therapy Systems, Llc System and method for fat and cellulite reduction
US9713731B2 (en) 2004-10-06 2017-07-25 Guided Therapy Systems, Llc Energy based fat reduction
US11235180B2 (en) 2004-10-06 2022-02-01 Guided Therapy Systems, Llc System and method for noninvasive skin tightening
US9827449B2 (en) 2004-10-06 2017-11-28 Guided Therapy Systems, L.L.C. Systems for treating skin laxity
US9827450B2 (en) 2004-10-06 2017-11-28 Guided Therapy Systems, L.L.C. System and method for fat and cellulite reduction
US9833639B2 (en) 2004-10-06 2017-12-05 Guided Therapy Systems, L.L.C. Energy based fat reduction
US9833640B2 (en) 2004-10-06 2017-12-05 Guided Therapy Systems, L.L.C. Method and system for ultrasound treatment of skin
US11207547B2 (en) 2004-10-06 2021-12-28 Guided Therapy Systems, Llc Probe for ultrasound tissue treatment
US9974982B2 (en) 2004-10-06 2018-05-22 Guided Therapy Systems, Llc System and method for noninvasive skin tightening
US10010721B2 (en) 2004-10-06 2018-07-03 Guided Therapy Systems, L.L.C. Energy based fat reduction
US11167155B2 (en) 2004-10-06 2021-11-09 Guided Therapy Systems, Llc Ultrasound probe for treatment of skin
US10010725B2 (en) 2004-10-06 2018-07-03 Guided Therapy Systems, Llc Ultrasound probe for fat and cellulite reduction
US10010724B2 (en) 2004-10-06 2018-07-03 Guided Therapy Systems, L.L.C. Ultrasound probe for treating skin laxity
US10046181B2 (en) 2004-10-06 2018-08-14 Guided Therapy Systems, Llc Energy based hyperhidrosis treatment
US10046182B2 (en) 2004-10-06 2018-08-14 Guided Therapy Systems, Llc Methods for face and neck lifts
US10238894B2 (en) 2004-10-06 2019-03-26 Guided Therapy Systems, L.L.C. Energy based fat reduction
US10960236B2 (en) 2004-10-06 2021-03-30 Guided Therapy Systems, Llc System and method for noninvasive skin tightening
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